EP3895620A1

EP3895620A1 - Method for gating in tomographic imaging system

Info

Publication number: EP3895620A1
Application number: EP21164530.4A
Authority: EP
Inventors: Sih-Yu Chen; Jhih-Shian Lee; Ya-Chen Chen
Original assignee: Delta Electronics Inc
Current assignee: Delta Electronics Inc
Priority date: 2020-04-13
Filing date: 2021-03-24
Publication date: 2021-10-20
Anticipated expiration: 2041-03-24
Also published as: US20210319599A1; EP4406483A2; EP3895620B1; TWI820411B; JP7177882B2; US20230290021A1; US11694374B2; JP2021168914A; CN113520432B; TW202137936A; EP4406483A3; US11954768B2; CN113520432A; ES2999674T3

Abstract

A method for gating in tomographic imaging system includes steps of:(a) performing a tomographic imaging on an object with a target moving periodically along a first axis (s) for acquiring projection images (Pθts); (b) obtaining projected curves (Cθts) by summing up pixel values along a direction of a second axis (t) perpendicular to the first axis (s) in each projection image (Pθts); (c) determining a target zone on the projection images (Pθts), wherein a central position on the first axis (s) of the target zone is corresponding to a position having the largest variation in the projected curves (Cθts) on the first axis (s); (d) calculating parameter values of pixel values in the target zones and obtaining a curve of a moving cycle of the target according to the parameter values; and (e) selecting the projection images (Pθts) under the same state in the moving cycle for image reconstruction according to the curve of the moving cycle of the target.

Description

FIELD OF THE INVENTION

The present disclosure relates to a method for gating in tomographic imaging system, and more particularly to a method for image-based gating in tomographic imaging system.

BACKGROUND OF THE INVENTION

Tomographic imaging system includes computed tomography (CT), positron emission tomography (PET), and single photon emission computed tomography (SPECT), etc. When the CT scan is performed, the light source (e.g. X-ray) and the detector are regularly moved around the detected object to emit x-ray and acquire image data by 180 (or more, or less) degrees, so as to collect the projection images at different angles. Based on the projection images, an image reconstruction is performed by the computer, and the cross-sectional tomographic image of the detected object is formed. Further, the three-dimensional image of the detected object is formed by the multiple tomographic images.
If the detected object is a living body, the organs (e.g. lung, heart) of the detected object may move periodically due to breath or heartbeat. Therefore, the organs of the detected object in the projection images at different angles are not static. Accordingly, the formed tomographic image would be blurred due to the movement of the organs.
The gating technique is developed for obviating blurred images caused by the periodical movement of the organs. Conventionally, the gating technique is a prospective gating technique, which is illustrated as follows.
In the prospective gating technique, the tomographic imaging system has to be connected with the external physiological monitoring apparatus, e.g., Electrocardiography (ECG) machine, piezoelectric sensor. The tomographic imaging system synchronizes with the physiological signal to acquire projection images in a specific state of period. An example of prospective gating for tomographic imaging is shown in FIG. 1. It is noted that the projection images are acquired only during the period marked by dashed blocks. Accordingly, the acquired multi-angle projection images under the same physiological period are utilized for image reconstruction. Consequently, the tomographic images under the specific physiological state are obtained, and blurred images caused by movement on the tomographic images can be reduced. However, the disadvantage of this prospective gating technique is that the tomographic imaging system has to be connected with the external physiological monitoring apparatus, which increases the cost a lot. In addition, it is also a technical challenge to synchronize the tomographic imaging system and the physiological monitoring apparatus.
Therefore, there is a need of providing a method for gating in tomographic imaging system to obviate the drawbacks encountered from the prior arts.

SUMMARY OF THE INVENTION

It is an objective of the present disclosure to provide a method for gating in tomographic imaging system. When the tomographic imaging is performed, the projection images are acquired continuously. After the projection images are all collected, the projection images are processed according to the characteristics thereof. Particularly, the projection images under the same physiological state are selected. Accordingly, in the method for gating in tomographic imaging system of the present disclosure, there is no need to connect the tomographic imaging system with any external physiological monitoring apparatus.
In accordance with an aspect of the present disclosure, there is provided a method for gating in tomographic imaging system. The method includes steps of: (a) performing a tomographic imaging on an object for acquiring a plurality of projection images at different angles, wherein a target of the object in the projection images moves periodically along a first axis; (b) obtaining a plurality of projected curves by summing up pixel values along a direction of a second axis, which is perpendicular to the first axis, in each of the projection images; (c) determining a target zone on the projection images, wherein the target is located in the target zone, and a central position on the first axis of the target zone is corresponding to a position having the largest variation in the projected curves on the first axis; (d) calculating parameter values of pixel values in the target zone on the projection images, and obtaining a curve of a moving cycle of the target according to the parameter values; and (e) selecting the projection images under the same state in the moving cycle for image reconstruction according to the curve of the moving cycle of the target.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 schematically shows the timing of performing tomographic imaging in the conventional prospective gating method;
FIG. 2 schematically shows the timing of performing tomographic imaging in a method for gating of the present disclosure;
FIG. 3 schematically shows the projection images taken at different angles;
FIG. 4 schematically shows the projection images taken at different angles and the corresponding projected curves;
FIG. 5 schematically shows the respiration curve obtained by the method for gating of the present disclosure; and
FIG. 6 is a schematic flow chart illustrating a method for gating in tomographic imaging system according to an embodiment of the present disclosure.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

The present disclosure will now be described more specifically with reference to the following embodiments. It is to be noted that the following descriptions of preferred embodiments of this disclosure are presented herein for purpose of illustration and description only. It is not intended to be exhaustive or to be limited to the precise form disclosed.
The method for gating in tomographic imaging system of the present disclosure utilizes a retrospective gating technique. When the tomographic imaging is performed, as shown in FIG. 2, the projection images are acquired continuously during the period marked by dashed block. Particularly, the present disclosure utilizes the retrospective gated tomographic imaging system for gating to obviate blurred images caused by the periodical movement of the organs due to breath or heartbeat.
When the tomographic imaging is performed, the light source, e.g., X-ray, and the detector are regularly moved around the detected object, so as to collect the projection images at different angles. If the detected object is a living body, the organs of the detected object may move periodically due to breath or heartbeat. Therefore, the projection images at different angles are not static. For example, the detected object is a mouse, and FIG. 3 shows the projection images of a mouse taken at different angles. The light source and the detector are rotated relative to the rotation axis which is depicted by the dashed line. The diaphragm of the mouse is located in the zone marked by the solid-line block, whose position is predetermined manually and needs to be further corrected. It is observed that the diaphragm moves upwardly or downwardly in different projection images due to breath.
In order to figure out the respiratory state to which every projection image is corresponding, the position of the organ or zone affected by breathing on the projection image should be detected. Taking the diaphragm as an example of a target that moves periodically in the detected object, the way of computing the position of the diaphragm is described as follows.
The light source and the detector rotate around the rotation axis to perform the tomographic imaging for the detected object. When the tomographic imaging is performed, the projection images at different angles are acquired continuously. The number of the projection images is N, being a positive integer, which can be determined according to the required image quality of the tomographic image formed based on the projection images. For example, the larger N is, the better the signal to noise ratio of the tomographic image is (i.e., the better the image quality of the tomographic image is). FIG. 4 schematically shows two projection images at two different angles. As shown in FIG. 4, the rotation axis is parallel to a first axis s, the diaphragm in the projection images moves upwardly or downwardly along the first axis s, and a second axis t is perpendicular to the first axis s.
According to equation (1), in N projection images P_θts of different angles θ, N projected curves C_θts are obtained by summing up the pixel values along the direction of the second axis t in every projection image. In all the angles θ that the N projection images are taken at respectively, the difference between the first angle and the final angle is preferably but not limited to be larger than 180 degrees. Moreover, in equation (1), T is the number of the pixels in the direction of the second axis t in the projection image. $C_{θts} = \sum_{t = 1}^{T} P_{θts}$
Taking FIG. 4 as an example, the projected curve is shown beside the corresponding projection image. The projected curve is a curve of the sum of the pixel values of each of the projection images versus the position along the first axis s. In particular, each point on the projected curve is corresponding to a pixel value summation and a position on the first axis s, where the said pixel value summation is the sum of the pixel values of all the pixels along the direction of the second axis t corresponding to the said position. That is, each of the projection images is projected along the first axis s to obtain the corresponding projected curve.
Then a diaphragm zone (target zone) where the diaphragm is located on the projection images is further determined. The diaphragm zone has a central position on the first axis corresponding to a position having the largest variation in the projected curves on the first axis s. For example, the projection image is regarded as a matrix of pixel values with a plurality of rows along the first axis s. The pixel values on each row are summed up to obtain the projected curve, and the row having the largest variation of the pixel value summation is the central position of the diaphragm zone. In an embodiment, in the N projected curves C_θts, the coefficients of variation or the standard deviations along the time sequence are calculated, and the position on the first axis s having the largest coefficient of variation or the largest standard deviation is the central position on the first axis s of the diaphragm zone. As shown in FIG. 4, the diaphragm zone in the projection image is marked automatically by a block, which is the solid-line block parallel to the second axis t. In specific, the dimension of the solid-line block is predetermined based on a general diaphragm size but not limited thereto. Once the central position of the diaphragm zone is determined, the diaphragm zone can be automatically marked by the block.
Since the detected object is always in the range of imaging during rotation, to sum up the pixel values along the second axis t can avoid the deviation caused by rotation. Therefore, the respiration curve obtained in the succeeding steps can be more accurate.
After the diaphragm zone is determined, the parameter value (e.g., maximum, minimum, average, median, summation or quartile) of the pixel values in the diaphragm zone on the projection image is calculated. Then the curve of the moving cycle of the diaphragm, i.e. the respiration curve, is obtained according to the parameter values. For example, the curve of the moving cycle of the diaphragm is a graph of the parameter value versus time, or a graph of the parameter value versus a serial number of the projection images.
As shown in FIG. 5, the respiration curve can be obtained according to the parameter values of the N projection images taken at different angles. The projection images under the same state in the respiratory cycle (i.e., the projection images taken at the same timing in the respiratory cycle) are selected for image reconstruction, and the definition of the diaphragm tomographic image is improved. For example, the projection images at the timing marked by the hollow circles are selected for image reconstruction, or the projection images at the timing marked by the solid circles are selected for image reconstruction. In FIG. 5, the transverse axis represents the time or the serial number of the projection images, and the vertical axis represents the parameter value of the pixel values.
FIG. 6 is a schematic flow chart illustrating a method for gating in tomographic imaging system according to an embodiment of the present disclosure. Based on the above illustration, the method for gating in tomographic imaging system of the present disclosure can be generalized to include the steps shown in FIG. 6.
First, in step S1, a tomographic imaging is performed on an object for acquiring a plurality of projection images at different angles. A target of the object in the projection images moves periodically along a first axis, which is parallel to a rotation axis of the light source and the detector.
Then, in step S2, a plurality of projected curves are obtained by summing up the pixel values along the direction of a second axis, which is perpendicular to the first axis, in each of the projection images.
Then, in step S3, a target zone on the projection images is determined. The target is located in the target zone, and a central position on the first axis of the target zone is corresponding to a position having the largest variation in the projected curves on the first axis. In an embodiment, in the projected curves, the coefficients of variation or the standard deviations along the time sequence are calculated, and the position having the largest coefficient of variation or the largest standard deviation is the central position of the target zone.
Afterward, in step S4, the parameter value of the pixel values in the target zone on each projection image is calculated, and a curve of the moving cycle of the target is obtained according to the parameter values of the projection images.
Finally, in step S5, the projection images under the same state in the moving cycle are selected for image reconstruction according to the curve of the moving cycle of the target.
In the embodiments shown in FIGS. 2-5, the detected object is a living body, and the target is the diaphragm, which moves periodically due to breath. Through the steps shown in FIG. 6, the projection images under the same state in the respiratory cycle are picked out for image reconstruction. Meanwhile, there is no need to connect the tomographic imaging system with any external physiological monitoring apparatus.
In another embodiment, the target may also be the heart, which moves periodically due to heartbeat, and the similar technique can also be applied to heart gating.
From the above descriptions, the present disclosure provides a method for gating in tomographic imaging system. When the tomographic imaging is performed, the projection images are acquired continuously. After the projection images are all collected, the projection images are processed according to the characteristics thereof. Particularly, the projection images under the same physiological state are picked out. Accordingly, in the method for gating in tomographic imaging system of the present disclosure, there is no need to connect the tomographic imaging system with any external physiological monitoring apparatus.

Claims

A method for gating in tomographic imaging system, characterized by comprising:
(a) performing a tomographic imaging on an object for acquiring a plurality of projection images (P_θts) at different angles (θ), wherein a target of the object in the projection images (P_θts) moves periodically along a first axis (s);

(b) obtaining a plurality of projected curves (C_θts) by summing up pixel values along a direction of a second axis (t), which is perpendicular to the first axis (s), in each of the projection images (P_θts);

(c) determining a target zone on the projection images (P_θts), wherein the target is located in the target zone, and a central position on the first axis (s) of the target zone is corresponding to a position having a largest variation in the projected curves (C_θts) on the first axis (s);

(d) calculating a parameter value of the pixel values in the target zone on each of the projection images (P_θts), and obtaining a curve of a moving cycle of the target according to the parameter values of the projection images; and

(e) selecting the projection images (P_θts) under the same state in the moving cycle for image reconstruction according to the curve of the moving cycle of the target.
The method according to claim 1, wherein the projected curve (C_θts) is obtained according to following equation: $C_{θts} = \sum_{t = 1}^{T} P_{θts},$
where C_θts is the projected curve, T is a number of pixels in the direction of the second axis (t) in the projection image (P_θts), and P_θts is the projection image.
The method according to claim 1, wherein when the tomographic imaging is performed, a light source and a detector are regularly moved around the object for acquiring the projection images (P_θts) at the different angles (θ).
The method according to claim 3, wherein the light source and the detector are rotated relative to a rotation axis parallel to the first axis (s).
The method according to claim 1, wherein a number (N) of the projection images (P_θts) is determined according to a required image quality of a tomographic image formed based on the projection images (P_θts).
The method according to claim 1, wherein each of the projection images (P_θts) is regarded as a matrix of pixel values with a plurality of rows along the first axis (s), the pixel values on each row are summed up, and the row having the largest variation of the sum of the pixel values in the projection images (P_θts) is the central position of the target zone.
The method according to claim 1, wherein in the projected curves (C_θts), coefficients of variation or standard deviations along a time sequence are calculated, and a position on the first axis (s) having a largest coefficient of variation or the largest standard deviation corresponds to the central position on the first axis of the target zone.
The method according to claim 1, wherein the parameter value is a maximum, a minimum, an average, a median, a summation or a quartile of the pixel values in the target zone.
The method according to claim 1, wherein the curve of the moving cycle of the target is a graph of the parameter value versus time, or a graph of the parameter value versus a serial number of the projection images (P_θts).